Method of and device for determining a nuclear magnetization distribution in a part of a body

ABSTRACT

The invention proposes a method and a device in which resonance signals (generated for NMR imaging) are sampled in the presence of a (semi-) static and a time modulated gradient magnetic field, the gradient direction of the fields applied being mutually perpendicular. The resonance signal is conditioned prior to the start of sampling. The sampled signals are associated with spatial frequencies (i.e. points in a spatial frequency space (k x , k y ) which is the (2-D) Fourier transform of the actual (x, y) space), which are determined by the applied gradient fields. The (semi-) static gradient field always produces an increase (for example, in k x ), while the time modulated gradient field always produces an image frequency which lies between two limits (k y  and k y  +k y ). Consequently, the invention enables the determination of data in an entire band in the (k x , k y ) space; this is in contrast with the present state of the art (DE 26.11.497) where data can be collected only along a straight line (k x  or k y  is constant), or on the entire region of interest (the total k x  , k y  space). The method and device according to the invention are also applicable for 3-D imaging of 3-D objects.

The invention relates to a method of determining a nuclear magnetization distribution in a part of a body which is situated in a stationary, homogeneous magnetic field which is generated in a first direction,

(a) a high-frequency electromagnetic pulse being generated whose magnetic field direction extends perpendicularly to the field direction of the homogeneous magnetic field in order to cause a precessional motion of the magnetization of nuclei in the body around the first field direction, a resonance signal thus being generated;

(b) after which either a first or a first and a second gradient magnetic field is applied during a preparation period, the gradient directions thereof being perpendicular to one another and the field directions being councident with the first direction;

(c) after which a further gradient field is applied for a measuring period, the gradient direction thereof being perpendicular to the gradient direction of at least one of the gradient magnetic fields mentioned sub (b), the field direction being coincident with the first direction, the measuring period being divided into a number of equally large sampling intervals for the periodic extraction of a number of (n) sampled signals from the resonance signal;

(d) after which, each time after a waiting period, the steps (a), (b) and (c) are repeated a number of times (n'), the integral of the intensity of at least one gradient field over the preparation period each time having a different value in order to obtain a group of sampling signals wherefrom, after Fourier transformation thereof, an image of the distribution of the induced nuclear magnetization is determined.

The invention also relates to a device for determining the nuclear magnetization distribution in a part of a body, comprising:

(a) means for generating a stationary homogeneous magnetic field,

(b) means for generating high-frequency electromagnetic radiation whose magnetic field direction is directed transversely to the field direction of the homogeneous magnetic field,

(c) means for generating at least one first and one second gradient magnetic field whose field directions coincide with the field direction of the homogeneous magnetic field and whose gradient directions are mutually perpendicular,

(d) sampling means for the sampling, in the presence of a gradient magnetic field generated by the means mentioned sub (c), of a resonance signal generated by means of the means mentioned sub (a) and (b), after the conditioning of the resonance signal with at least one gradient field generated by the means mentioned sub (c),

(e) processing means for the processing of the signals supplied by the sampling means, and

(f) control means for controlling at least the means mentioned sub (b) to sub (e) for the generating, conditioning, sampling and processing of a number of resonance signals, each resonance signal being each time conditioned during a preparation period, the control means supplying the means mentioned sub (c) with control signals for the adjustment of the intensity and/or duration of at least one gradient magnetic field, the integral of the intensity over the duration of at least one gradient magnetic field being different after each waiting period.

Such a method (also referred to as Fourier zeugmatography) and device are known from DE-OS 26.11.497. According to such a method, a body to be examined is subjected to a strong, stationary, homogeneous magnetic field B_(o) whose field direction coincides with, for example, the z-axis of a Cartesian coordinate system (x, y, z). The stationary magnetic field B_(o) causes a slight polarization of the nuclear spins present in the body and enables a precessional motion of nuclear spins around the direction of the magnetic field Bo. After the application of the magnetic field Bo, a preferably 90° pulse of a high-frequency electromagnetic radiation is generated (with an angular frequency ω=γ. Bo, in which γ is the gyromagnetic ratio and Bo is the intensity of the magnetic field), which rotates the magnetization direction of the nuclei present in the body through an angle (90°). After termination of the 90° pulse, the nuclear spins will perform a precessional motion around the field direction of the magnetic field Bo, thus generating a resonance signal (FID signal). Using the gradient magnetic fields G_(x), G_(y), G_(z) whose field directions coincide with that of the magnetic field Bo and which have a gradient in the x, the y and the z-direction, respectively, a total magnetic field B=Bo+G_(x) ·x+G_(y) ·y+G_(z) ·z can be generated.

After the 90° pulse, a field gradient G_(x) is applied for a period t_(x), and subsequently a field gradient G_(y) for a period t_(y), so that the precessional motion of the excited nuclear spins is influenced in a location-dependent manner. After this preparation phase (i.e. after t_(x) +t_(y)), a field gradient G_(z) is applied and the FID signal (actually the sum of all magnetizations of the nuclei) is sampled at N_(z) measuring instants during a period t_(z). The described measuring procedure is subsequently repeated 1×m times, each time different values being used for t_(x) and/or t_(y). Thus, (N_(z) ×m×1) samples are obtained which contains the information concerning the magnetization distribution in a part of the body in the space x, y, z. The 1×m sampled signals each of N_(z) samples are each time stored in a memory (in N_(z) ×m×1 memory locations), after which an image of the nuclear magnetization distribution is obtained by a 3-D Fourier transformation of the sampled signals of the FID signals.

Obviously, it is alternatively possible, using selective excitation, to generate only the FID signal of nuclear spins in a 2-dimensional slice (having an orientation which can be selected at random) so that, for example, an FID signal need be generated only m times in order to obtain an image of the magnetization distribution in m×N_(z) points in the selected slice by way of a two-dimensional Fourier transformation. It will be clear that when use is made of the Fourier zeugmatography method, the time required for forming an image of the magnetization distribution may be as high as a few minutes. Such a measuring period is unacceptably long for a patient being examined who must remain motionless during this period.

The invention proposes a method which substantially reduces the time required to form an image having a resolution which equals that obtained when the Fourier zeugmatography technique is used.

To this end, a method in accordance with the invention is characterized in that during the measuring period an additional gradient magnetic field is generated whose gradient direction corresponds to the gradient direction of a gradient magnetic field generated during the preparation period and whose field direction coincides with the first direction, the additional gradient magnetic field being periodic in time and having a period which is equal to the sampling interval, the effect exerted on the nuclear magnetization by the additional gradient magnetic field, integrated over a sampling interval being zero, at least one additional sampling operation being performed after the beginning and before the end of each sampling interval.

In accordance with the invention, in the presence of the generated FID signal an additional time-modulated gradient field is applied, so that one or even several additional FID signal sampling operations are performed during the period between two sampling operations (determined by the size of the body and the resolution in its image of a nuclear magnetization distribution in the known Fourier zeugmatography). Per measuring cycle (preparation period+measuring period+waiting period), therefore, at least twice as many (p times as many) samples are obtained, so that the number of measuring cycles to be performed is halved (or reduced by a factor p).

It is to be noted that a method is known for the determination of a nuclear magnetization distribution in which during a single measuring cycle (i.e. from one FID signal) such information is derived, by utilizing time-modulated gradient fields, and that therefrom a two-dimensional nuclear magnetization distribution can be reconstructed. This method is referred to as the "echo-planar method" and is described in an article by P. Mansfield and I. L. Pykett, entitled "Biological and Medical Imaging by NMR", published in Journal of Magnetic Resonance, 29, 1978, pages 355-373, and also in an article by L. F. Feiner and P. R. Locher, entitled: "On NMR Spin Imaging by Magnetic Field Modulations", published in Applied Physics 22, 1980, pages 257-271. The echo-planar method utilizes time-dependent magnetic field gradients during the measurement of the FID signal. The echo-planar method enables a complete two-dimensional image to be obtained within the duration of a single FID signal. The determination of the nuclear magnetization distribution in a slice of the body to be examined is achieved by using, in addition to the uniform magnetic field, for example in the z-direction, for example, a magnetic field gradient G_(z) in the same direction and at the same time a (90°) high-frequency, amplitude-modulated pulse in order to generate an FID signal in a slice having an effective thickness Δz. Immediately after the high-frequency pulse, the gradient field G_(z) is switched off and the FID signal is measured, for example, with an alternating gradient field G_(x) and a stationary gradient field G_(y) (image of the x-y slice).

The number of measuring points required for a complete 2-dimensional image is measured with a single FID signal according to the echo-planar method. In order to achieve the resolution required in practice, the gradient which periodically alternates in time must have a high frequency and a high intensity when this echo-planar method is used. This causes large variations (dB/dt) of the gradient magnetic field; which is undesirable for a patient. The intensity of the gradient fields used in the method in accordance with the invention is substantially lower than the intensity of the gradient fields used in the echo-planar method. Consequently, the variations of the field strength caused by modulation are also substantially smaller, which is an advantage.

The invention will be described in detail hereinafter with reference to the embodiments shown in the drawing; therein:

FIG. 1a shows a coil system which forms part of a device for performing a method in accordance with the invention;

FIG. 1b diagrammatically shows the shape of the x/y gradient coils;

FIG. 1c shows a shape of coils generating a high-frequency field;

FIG. 2 shows a device for performing a method in accordance with the invention;

FIG. 3a and 3b illustrate a simple version of a method in accordance with the invention;

FIG. 4 shows a further version of a method in accordance with the invention;

FIG. 5 shows the instants at which sampling must take place for a sinusoidal gradient and the lines to be measured;

FIG. 6 shows a further embodiment of a part of the device in accordance with the invention.

FIG. 1a shows a coil system 10 which forms part of a device used for determining a nuclear magnetization distribution in a part of a body 20. This part has a thickness of, for example, Δz and is situated e.g. in the x-y plane of the coordinate system x.y.z. shown. The y-axis of the system extends upwards, perpendicularly to the plane of drawing. The coil system 10 generates a uniform stationary magnetic field B_(o) having a field direction parallel to the z axis, three gradient magnetic fields G_(x), G_(y) and G_(z) having a field direction parallel to the z axis and a gradient direction parallel to the x, y and z axis, respectively, and a high-frequency magnetic field. To this end, the coil system 10 comprises some main coils 1 for generating the stationary uniform magnetic field B_(o) having an intensity of some tenths of a tesla. The main coils may be arranged, for example, on the surface of a sphere 2 whose centre is situated in the origine 0 of the Cartesian coordinate system x, y, z, the axes of the main coils 1 being coincident with the z axis.

The coil system 10 furthermore comprises, for example, four coils 3_(a), 3_(b) which are arranged for example on the same spherical surface and which generate the gradient magnetic field G_(z). To this end, a first set 3a is excited by a current in the opposite sense with respect to the current direction in the second set 3b; this is denoted by ○. and ○x in the Figure. Therein, ○x means a current entering the section of the coil 3 and ○x means a current leaving the section of the coil.

The coil system 10 comprises, for example, four rectangular coils 5 (only two of which are shown) or four other coils such as, for example, "Golay coils" for generating the gradient magnetic field G_(y). In order to generate the gradient magnetic field G_(x), use is made of four coils 7 which have the same shape as the coils 5 and which have been rotated through an angle of 90° around the z axis with respect to the coils 5. For a better impression of the shape of the coils 7 (and 5), a perspective view is given in FIG. 1b. The direction in which an electric current passes through the coils 7 is denoted by arrows 9.

FIG. 1a also shows a coil 11 whereby a high-frequency electromagnetic field can be generated and detected. FIG. 1c is a perspective view of the coil 11. The coil 11 comprises two halves 11a and 11b which are electrically interconnected so that the current directions denoted by arrows 13 are obtained during operation.

FIG. 2 shows a device 15 for performing a method in accordance with the invention. The device 15 comprises coils 1, 3, 5, 7 and 11 which have already been described with reference to the FIGS. 1a, b, c, current generators 17, 19, 21 and 23 for the excitation of the coils 1, 3, 5, and 7, respectively, and a high-frequency signal generator 25 for the excitation of the coil 11. The device 15 also comprises a high-frequency signal detector 27, a demodulator 28, a sampling circuit 29, processing means such as an analog-to-digital converter 31, a memory 33 and an arithmetic circuit 35 for performing a Fourier transformation, a control unit 37 for controlling the sampling instants and also a display device 43 and central control means 45 whose functions and relationships will be described in detail hereinafter.

The device 15 performs a method for determining the nuclear magnetization distribution in a body 20 as will be described hereinafter. The method comprises several steps. Before the "measurement" is started, the nuclear spins present in the body are excited to resonance. The resonance excitation of the nuclear spins is performed by the switching on of the current generator 17 by the central control unit 45, so that the coil 1 is excited. A stationary and uniform magnetic field B_(o) is thus generated. Furthermore, the high-frequency generator 25 is switched on for a brief period of time, so that the coil 11 generates a high-frequency electro-magnetic field (r.f. field). The nuclear spins in the body 20 can be excited by the applied magnetic fields, the excited nuclear magnetization enclosing a given angle, for example, 90° (90° r.f. pulse) with respect to the uniform magnetic field B_(o). The location where and which nuclear spins are excited depends inter alia on the intensity of the field B_(o), on any gradient magnetic field to be applied, and on the angular frequency ω_(o) of the high-frequency electromagnetic field, because the equation ω_(o) =γB_(o) (1) is to be satisfied, in which γ is the gyromagnetic ratio (for free protons, for example, and for H₂ O protons, γ/₂π =42.576 MHz/T). After an excitation period, the high-frequency generator 25 is switched off by the central control means 45. The resonance excitation is performed each time at the beginning of each measuring cycle. For some embodiments further r.f. pulses are induced in the body. The r.f. pulses are a first 90° r.f. pulses and a series composed of 180° (as well as 90°) r.f. pulses which are periodically induced into the body. The first case is referred to as "spin-echo". Spin echo is inter alia described in the article by I. L. Pykett "NMR Imaging in Medicine", published in Scientific American, May 1982.

During a next step, usable samples are collected. For this purpose use is made of the gradient fields which are generated by the generator 19, and 21, 23, respectively, under the control of the central control means 45. The detection of the resonance signal (referred to as FID signal) is performed by the switching-on of the high-frequency detector 27, the demodulator 22, the sampling circuit 29, the analog-to-digital converter 31 and the control unit 37. This FID signal appears as a result of the precessional motion of the nuclear magnetizations around the field direction of the magnetic field B_(o) due to the r.f. excitation pulse. This nuclear magnetization induces an induction voltage in a detection coil whose amplitude is a measure for the nuclear magnetization.

The analog, sampled FID signals originating from the sampling circuit 29 are digitized (converter 31) and stored in a memory 33. After expiration of the measuring period T, the central control means 45 deactivates the generators 19, 21 and 23, the sampling circuit 29, the control unit 37 and the analog-to-digital converter 31.

The sampled FID signal is stored in the memory 33 and, after Fourier transformation in the arithmetic circuit 35, it produces a spectrum whose amplitudes contain data concerning nuclear magnetizations. Unfortunately, in a 2D or 3D image translation from spectrum to location is not possible. Therefore, the resonance signal produced by the arithmetic circuit 35 is first stored in the memory 33. The method used for the translation to location depends on the use of the gradient magnetic fields.

The method in accordance with the invention notably concerns an imaging aspect of NMR. For a proper understanding of the invention, it is necessary to consider first the theory of NMR imaging. This will be done on the basis of a simple case involving the imaging of a one-dimensional object (referred to hereinafter as 1-D).

Assume that the object, containing NMR-active nuclei such as, for example, protons, is present in a homogeneous magnetic field B_(o). Using a radio-frequency excitation pulse (90° r.f. pulse), a magnetization of nuclei transverse to the magnetic field B_(o) is obtained. After the excitation, a gradient magnetic field is added to the B_(o) field during a preparation period. This gradient extends in the direction of the 1-D object which is arranged, for example, along the x axis of an x, y, z reference system. The gradient magnetic field is then described by: ##EQU1## in which x is a unity vector in the x direction. It is to be noted that when the gradient magnetic field G_(x) is homogeneous, which means that G_(x) is independent of x, it describes a linear variation between the intensity of the magnetic field and the x coordinate. In the presence of G_(x) the nuclear magnetizations will perform a precessional motion with a frequency which is dependent on their coordinate in accordance with the relation

    ω(x)=ω.sub.o +γ·G.sub.x ·x (3)

Now, the signal induced in the coil does not consist of a single frequency ω_(o), but of a series of frequencies ω(x). By performing a Fourier analysis of the measured signal, the intensity of the precessional nuclear magnetization can be determined as a function of the frequency. Because the frequency is now unambiguously dependent on the coordinate (expression (3)), the nuclear magnetization has been determined as a function of the x coordinate, so that an NMR image of the 1-D object has been made. The image information is then formed by the magnitude of the nuclear magnetization. Obviously, this is co-determined by the density ρ of the NMR-active nuclei, but in general other parameters such as the spin lattice relaxation time T₁ and spin-spin relaxation time T₂ also have an effect on the image obtained.

The induction voltage to be measured is quadrature-detected. This means that the signal is mixed with a reference signal which generally has the same frequency ν_(o) as the radio-frequency excitation pulse. The measured signal is thus shifted on the frequency axis, the shift amounting to ν_(o). For quadrature-detection, the signal is mixed once with a first reference having a phase φ with respect to the radio-frequency signal used for the excitation, and once with a second reference (φ+90°) which has the same frequency but whose phase has been shifted 90° with respect to the first reference.

This means that in a coordinate system which performs a precessional motion at a frequency ω_(o) =2πν_(o) around B_(o), the components of the total nuclear magnetization are determined, that is to say the components in a system which is stationary within the rotating system and one of the axes of which encloses an angle φ with respect to the axis along which the r.f. field B₁ is directed during the excitation. Thus, when φ=0, the components of the total nuclear magnetization are determined which are in phase and in 90° shifted phase, respectively, with respect to the r.f. field of the excitation pulse. By utilizing a quadrature-detection, a distinction can be made between clockwise and counterclockwise rotating magnetizations in the rotating system. Accordingly, after quadrature-detection positive and negative frequencies can be distinguished. When the 1-D object is symmetrically arranged around the original (which is the point in which the gradient does not contribute to the external field), after the quadrature-detection the signal will be situated in the frequency band extending from -ω₁ to +ω₁. Therein, ω₁ =γ·G_(x) ·1 in which 1 is half the length of the object. The two signals obtained after quadrature-detection will be referred to hereinafter as the real and the imaginary signal, respectively. The Fourier transformation of these signals can not be described in a complex manner. The complex time signal

    f(t)=f.sub.1 (t)+i.f.sub.2 (t)                             (4)

is written as follows after the Fourier transformation: ##EQU2## in which ##EQU3## Thus, the spectrum g(ω) is now also complex. It has been assumed in the foregoing that the functions f₁ and f₂ on the entire time axis are known as continuous functions. In practice, however, this is not simply the case and the low-frequency signals f₁ and f₂ are measured by sampling. Obviously, this is subject to the sampling theorema: when a signal is to be unambiguously defined, at least two samples must be taken per period of the highest frequency occurring. For the 1-D object, this is

    ν.sub.1 =ω.sub.1 /(2π)                         (6)

The sampling interval t_(m), which is the period of time expiring between two successive sampling operations, must than at least be ##EQU4## Conversely, for a sampling interval t_(m) of the real as well as the imaginary signal, the width of the frequency band is 1/t_(m). When n equidistant samples are taken from the real as well as the imaginary time signal, g₁ (ω) as well as g₂ (ω) will also be described by n points. The spacing of these points in the frequency space, therefore, is ##EQU5## The more points are taken in the time interval for the same t_(m), that is to say the longer measuring is performed, the finer the resolution in frequency space will be (real as well as imaginary) and hence also the resolution in the image-space.

Resolution enhancement can also be achieved in another manner, for example, by making the gradient twice as strong. In that case the object will correspond to a bandwidth which is twice as large. In that case sampling must be twice as fast. When 2n samples are taken on the time signal, the total measuring time will be the same again, but the frequency band will be divided into 2n intervals. Because the object fills the entire band, this means that 2n space intervals Δx are situated on the object 2n. Thus, the resolution will be twice as high. An example will now be described for the purpose of illustration. Consider a 1-D object which contains protons, has a length 2l=10 cm and is situated in a gradient field G_(x) =23.49 10⁻⁴ T/m; a frequency band ν₁ =Γ·G_(x) ·2·1/2π=10 kHz then corresponds to the length of the object. Because the object is symmetrically arranged around the origin, the highest frequency occurring is 5 kHz, so that for the sampling intervals t_(m) =100 μs is chosen. When, for example, 128 samples are taken, the signal is measured during 12.8 ms.

After Fourier transformation, the frequency-intervals amount to (n·t_(m))⁻¹ =78 Hz. This corresponds to ##EQU6## so that Δx=0.78 mm for each space interval.

As has already been stated, several possibilities exist for the douvling of the resolution. The first possibility is to keep the gradient the same, and also t_(m), and to double the number of samples; thus, in the above case 256 samples instead of 128 samples. The overall measuring period then beocmes 25.6 ms. The frequency intervals after Fourier transformation are then ##EQU7## which corresponds to Δx=39/10.000×100 mm=0.39 mm as the length for each space interval. In the second case, the gradient becomes twice as large: G_(x) =46.98 10⁻⁴ T/m. A body-length of 10 l cm then corresponds to a bandwidth of 20 kHz. The highest frequency is then 10 kHz and, consequently, t_(m) amounts to 50 μs. When 256 samples are taken, measurement of the signal again requires 12.8 ms. In the frequency domain the intervals are then (n·t_(m))⁻¹ =78 Hz, which again corresponds to Δx=78/20,000·100 mm=0.39 mm. Summarizing it may be stated that a higher resolution is obtained either by longer measuring periods or by utilizing larger gradients. Evidently, combinations thereof are also feasible. It is to be noted, however, that larger gradients generally cause more noise. On the other hand, the measuring period cannot be indefinitely prolonged because of relaxation effects whilst, moreover inhomogeneities in the magnetic field B_(o) may lead to unacceptable distortion of the image in the case of weak gradients. A compromise will usually be chosen in practice.

The entire problem can also be approached in a different manner. Let us again consider a 1-D object with the coordinate x. The spatial Fourier transform of this image then has a coordinate k_(x) and describes the spatial frequencies ("lines per cm") used to compose the image. In first instance one would think that the image function F(x) is a real function. In NMR imaging utilizing quadrature-detection, the distribution of two of the three components of the nuclear magnetization is measured. This is because the components perpendicular to B_(o) produce an induction voltage in the radio-frequency coil. Each of the components can be described by an image function, or in other words F(x) is a function which consists of two parts, F₁ (x) and F₂ (x) which describe the magnitude of the mutually perpendicular components (each of which is perpendicular again to B_(o)) as a function of the coordinate x. This is written as F(x)=F₁ (x)+i.F₂ (x). The complex Fourier transform G(k_(x))=G₁ (k_(x))₋₋ i G₂ (k_(x)) is found from: ##EQU8## It is to be noted that k_(x) ·x represents a phase angle. In 1-D spin imaging, via the gradient G_(x) there is a one to one correspondance between the location x and the NMR frequency ω_(x) in accordance with the relation

    ω.sub.x =ω.sub.o +γ·G.sub.x ·x

Because of the quadrature-detection of the signals, the frequency ω_(o) will be ignored hereinafter. At a given instant t after the application of the constant gradient G_(x) a magnetization at the location x has a phase γ·G_(x) ·x·t with respect to the phase at the instant t=0. γ·G_(x) ·t may now interpreted as the spatial frequency k_(x). When the gradient is not constant, the phase angle of the magnetization at the instant t is given by ##EQU9## is associated with k_(x). When the signals f₁ (t) and f_(x) (t) are measured a period t after the application of the gradient G_(x), they will be equal to G₁ (k_(x)) and G₂ (k_(x)), respectively, except for a constant. Here ##EQU10## The constant depends on various instrumental parameters, such as quality factor of the coil, gain factors of r.f.-amplifiers, etc. Because nothing but only the variation of the nuclear magnetization is determined, an absolute measurement is not important and the constant can be ignored hereinafter.

Because the origin has been chosen in the image space in the centre of the object, the origin in the spatial frequency space is also chosen in the centre. Thus, negative spatial frequencies are also permitted. The value of these frequencies can be determined, for example, by measurement of the signal after a constant, negative gradient has been present for a given period t. In practice, usually negative and positive spatial frequencies are measured in one FID. This can be done, for example, by first initiating a negative gradient until the minimum k_(x) is reached prior to the sampling of the signal. Subsequently, the sign of the gradient is reversed and the signal is sampled. During sampling, the spins will all be in phase again at a given instant, provided that the effects of inhomogeneities in the static magnetic field are ignored or somehow compensated for (for example, by using a spin-echo technique). This instant corresponds to t=0. At this instant the phases of the spins are such as if no gradient has been active yet. At instants before this point, the negative spatial frequencies are measured, whilst after this point the positive spatial frequencies are measured. A real and an imaginary image can be reconstructed on the basis of these frequencies.

Summarizing, it may be stated that when the two components of the signal (real and imaginary) are measured at a given instant t with respect to the reference instant t=0, the amplitude of the image frequency ##EQU11## has been unambiguously defined. When the two measured values are referred to as G₁ and G₂, respectively, they represent a sinusoidal intensity modulation in the real and the imaginary image (complex image wave) whose wave-length equals ##EQU12## The phase of this image wave, measured in the origin x=0 (which means at the point where the gradient does not contribute to the field) is given by arc tan (G₂ /G₁), i.e. by the phase angle of the signal at the instant t. The amplitude of this wave is

    (G.sub.1.sup.2 +G.sub.2.sup.2).sup.1/2.

Because only a finite number of spatial frequencies are measured, the resolution is limited. The resolution can be enhanced by measuring higher spatial frequencies (positive as well as negative). Because ##EQU13## this can be achieved, for example, by prolonging the measurement or by increasing the gradient. This is in accordance with the foregoing.

The question is now which spatial frequencies should actually be measured in order to obtain an image having a given resolution. For the answer to this question, reference is made to the previous description of the sampling of the signal. When the gradient G_(x) is constant, it must be insured that at least two additional sampling operations are performed per period of the highest frequency occurring. This implies a sampling interval of less than π/ω₁. This means that the magnetization associated with the highest frequency ν₁ occurring is rotated slightly less than 180° from one sampling operation to another. When the sampling interval is again denoted by t_(m), therefore Γ·G_(x) ·1·t_(m) is slightly smaller than π, so Γ·G_(x) ·t_(m) is slightly smaller than π/1. For a reproduction of the complete object having a length of 21 in n points, the signal must also be sampled n times using this t_(m).

This can be translated into a sampling of k_(x) points. The sampling interval t_(m) corresponds to an interval Δk_(x) =Γ·G_(x) ·t_(m) (10), and this should be slightly smaller than π/1=2·π/L (11), in which L=21, i.e. the total length of the 1-D object. The fact that it is necessary to measure at n different instants at intervals t_(m) in order to achieve a resolution of n points can be translated into a measurement at n different k_(x) values with interval Δk_(x).

As has already been stated, the aim is to measure the spatial frequencies which are central around k_(x) =0. For the sampling in the presence of a constant gradient magnetic field G_(x), this means that they must be centred around the instant at which the gradient field G_(x) does not make an effective contribution ##EQU14## to the phase of the nuclear magnetization.

On the basis of this knowledge it is also possible to attack the problem of the imaging of 2-D and 3-D objects. It is to be noted that the selective excitation technique can be used to ensure that image information is collected only from a thin slice of a 3-D object, so that the use of a 2-D technique need not be restricted to actual 2-D objects.

Completely analogously to the 1-D method, now an image function F(x, y)=F₁ (x, y)+iF₂ (x, y) is defined whose spatial Fourier transform G(k_(x), k_(y)) is: ##EQU15## G is complex again: G(k_(x),k_(y))=G₁ (k_(x),k_(y))+iG₂ (k_(x),k_(y)). Both components G₁ and G₂ and be identified again with the two components of the time signal, for which ##EQU16## Therein, G_(y) is a gradient in the y direction ##EQU17## Actually, the spin-imaging experiment again is the determination of the values of the spatial frequencies (k_(x), k_(y)), the resolutions in the x and the y direction, respectively, again being determined by the highest spatial frequencies k_(x) and k_(y) still measured. The expansion to the 3-D case can be simply realized by introduction of ##EQU18##

However, for the sake of simplicity the description will be restricted to the 2-D case. The determination of the intensities of the spatial frequencies (k_(x), k_(y)) is performed by measurement of the FID signal after the magnetizations have been subjected to the effect of the gradient G_(x) and G_(y) for a period t. Then: ##EQU19##

It is to be noted that the above description also holds when the spin-echo technique is used. However, in that case the sign of the results of the integrals ##EQU20## must be changed each time a 180° r.f. pulse is applied at instants t₂. Here t₁ is the instant after application of a preceding 180° r.f. pulse. The sign of the results of the integrals must be changed, because the effect exerted by the gradient field G_(i) until the instant t₂ is the same as if the gradient field G_(i) had the opposite direction and no 180° r.f. pulse had been applied.

The signals are again sampled in the 2-D case. This means that only the value of given spatial frequencies is determined. These spatial frequencies may form a rectangular lattice in the (k_(x), k_(y)) space, but in principle any type of lattice is feasible (polar or rhombic lattices). A polar lattice is used in the so-called projection reconstruction (see, for example, P. R. Locher, Nederlands Tijdschrift voor Natuurkunde, A47, (3), 114, 1981). For the description reference will only be made to a rectangular lattice, but this is not a restriction. According to the known Fourier zeugmatography the magnetizations are first exposed to the effect of, for example, G_(y) for a given period of time. After G_(y) has been switched off, the signal is measured in the presence of G_(x). Sampling at the instant t again defines the value of the spatial frequency ##EQU21## In this diagram the information is collected on a line in the (k_(x), k_(y)) space which extends parallel to k_(y) =0. For the measurement of all desired spatial frequencies, this diagram must be repeated for other values of ##EQU22## In practice this is usually done by variation of the amplitude and/or duration of G_(y) from one measurement to another.

The question now is how a given object must be sampled in order to obtain a desired resolution N_(x) ×N_(y). When the total dimension of the object in the i^(th) direction (i=x, y) is L_(i), the distance Δk_(i) between two successive values of k_(i) at which measurement takes place must be less than 2π/L_(i). For a resolution of N_(i) points in the i^(th) direction, measurement must be performed at N_(i) different values of k_(i), said k_(i) values requiring a spacing equal to Δk_(i).

An embodiment of a method in accordance with the invention will be described with reference to the FIGS. 2, 3a and b. Using the high frequency coil 11, a 90° pulse P1 is generated after the activation of the main coils 1 which generate the stationary homogeneous magnetic field B_(o). The resonance signal F1 then occurring is allowed to decay when using a spin-echo technique and after a period of time t_(v1) a 180° pulse P2 is generated by the high frequency coil 11. During a part of the period t_(v1) a gradient field G_(x) (denoted by a curve G1) is generated for reasons yet to be described. After a period of time t_(v2), being equal to t_(v1), an echo resonance signal F2 produced by the 180° pulse P2 will generally reach a peak value. This instant t_(o) will be defined as the instant t=0. The use of the so-called spin-echo technique (180° pulse P2) prevents the occurrence of phase errors in the resonance signals. Such errors are caused by inhomogeneities in the stationary magnetic field B_(o). The echo-resonance signal F2 is sampled at sampling intervals t_(m) during which a gradient magnetic field G_(x) (denoted by a curve G2) is present. The sample obtained are associated with the various k_(x) values ##EQU23## As has already been deduced, positive as well as negative k_(x) values should be determined. Consequently, during the period t_(v1) also a gradient field G_(x) is generated whose value ##EQU24## It is thus achieved that the overall effect of the gradient magnetic field G_(x) on the nuclear spins in precessional motion is nil at the instant t_(o) ##EQU25## so that at the instant t_(o) a sample of the resonance signal is taken which is associated with the spatial frequency k_(x) =0. In other words, the foregoing means that thanks to the application of the gradient magnetic field G_(x) during t_(v1) it is achieved that at the starting instant t_(s) of a measuring period T=N·t_(m) sampling operation is performed which is associated with the most negative frequency k_(x), a less negative spatial frequency k_(x) being associated with each subsequent sample (for t_(o), k_(x) =0) until ultimately at the end t_(e) of the measuring period T a sample is taken which is associated with the most positive spatial frequency k_(x).

According to the foregoing, when no gradient magnetic field G_(y) is applied, spatial frequencies k_(x) are determined at which the spatial frequency k_(y) is always zero. In FIG. 3b the amplitudes of the samples taken are plotted on a k_(x) -k_(y) slice. The described sampling method results in a graph S1 along the line k_(y) =0. The distance Δk_(x) between the positions of the samples in the k_(x) -k_(y) plane is determined by the formula ##EQU26## in which t_(m) is the sampling interval.

When a gradient magnetic field G_(y) is applied during the period t_(v1) (the period of time between the 90° pulse P1 and the 180° pulse P2), denoted by a broken line in FIG. 3 in the G_(y) -t graph, the integral ##EQU27## will be unequal to zero at the beginning of the measuring time T and samples will be taken which are associated with the spatial frequency pairs (k_(x), k_(y)). The spatial frequency k_(y) does not change during the measuring period T and the frequencies k_(x) again increase from most negative to most positive. In other words, in FIG. 3b on a line k_(y) 16 0 samples are inserted as a function of k_(x), the distance Δ between the two lines k_(y) =0 and k_(y) ≠0 being determined by ##EQU28## The samples are denoted by 0 in FIG. 3b. The associated sampling instants are also denoted by 0 in FIG. 3a. It will be clear that the distance Δ between two lines can be adjusted by variation of the intensity of the gradient field G_(y) or by variation of the period of time during which the gradient magnetic field G_(y) is present or both. In the method in accordance with the invention, during the measuring period T a (time modulated) additional gradient magnetic field G_(y) is applied which is denoted by the curve G₃ in FIG. 3a. The additional gradient magnetic field G_(y) is modulated so that: ##EQU29## so that samples can be taken which are associated with different values of k_(y) within a sampling interval t_(m), the original samples which are denoted by 0 in FIG. 3a not being disturbed thereby.

Because the above integral is not zero between the instants denoted by 0 and X in FIG. 3a, a maximum distance from the line L1 is reached after one half period t_(m) (assuming that G_(y) is sinusoidal (G₃) or square-wave (G₄)): ##EQU30## When sampling is performed at the instants which are indicated by x in FIG. 3a, these samples will be associated with a line L2 which extends parallel to the line L1 at a distance Δk_(y). The points situated on the line L2, however, have been shifted through 1/2. Δk_(x) in the k_(x) direction, because the gradient field in the x direction also has its effect during said first half period of G₃ (or G₄). This shift can be avoided by modulating the gradient magnetic field G_(x) in such a way that a the gradient direction is not reversed (the measurements range from -k_(x) to +k_(x)) and b the gradient magnetic field G_(x) ' has an intensity zero during the part of the sampling interval t_(m) during which sampling operations are performed. These parts are denoted by t_(x) in FIG. 3a and are plotted in a G_(x) '-t graph which shows an example of a modulated gradient magnetic field G_(x) '.

The sampling interval t_(m) depends on the size of the object and the strength of the gradient field. In general the sampling interval t_(m) has a value between 10-100 μs in the known Fourier zeugmatography. The method in accordance with the invention utilizes the duration of the sampling interval for performing at least one further sampling operation during the interval t_(m) (denoted by x in FIG. 3a). It is to be noted that two signals are to be sampled, even though only one amplitude value (for each instant) of the resonance signal is shown in FIG. 3a and in FIG. 3b (for some k_(y) value). As has already been explained these two signals are obtained by means of quadrature-detection of the resonance signal. It is also to be noted in the case of use of the spin echo technique as described above there will virtually exist a point-symmetry with respect to the point k_(x) =k_(y) =0, so that actually sampling operations are required, for example, either for all k_(x) (from negative to positive maximum), where k_(y) ≧0, or for all k_(y) (from negative to positive maximum), where k_(x) ≧0. The graph as shown in FIG. 3b is point-symmetrical, but the imaginary k_(x) -k_(y) graph is anti-symmetrical with respect to k_(x) =k_(y) =0.

The periodic variation of G_(y) during the period of the sampling interval t_(m) is chosen so that the additional phase coding produced by G_(y) at the end of each sampling interval is nil ##EQU31## It this were not so, the samples at the beginning of each next sampling interval would no longer be situated on the reference line L1 but would be shifted along the k_(y) -axis. Consequently, each point thus measured is associated each time with a different value of k_(y). Because it is attractive for the processing of the samples that these points are associated with a rectangular k_(x) -k_(y) lattice, such a measuring method is inefficient and necessitates additional calculations. The above integral ##EQU32## means that the surfaces enclosed by the curve of G_(y) (in FIG. 3) for G_(y) >0 and G_(y) <0 must be the same within a sampling interval.

When the applied gradient magnetic field G_(x) is constant in time, the sampling interval t_(m) should be slightly smaller than 2π/(Γ·G_(x) ·L_(x)), as has already been deduced. When oversampling is used during sampling (for example, to eliminate noise by way of digital filtering), obviously the period of G_(y) must be adapted thereto. The amplitude G_(y) follows directly from the requirement that an interval Δk_(y) must be bridged in one half period of G_(y) (t). For the further description it will be assumed that the sampling intervals t_(m) on a line parallel to k_(y) =0 are equal to 2π/Γ·G_(x) L_(x) (12). Fold-back effects which could be caused thereby can be prevented by choosing the object to be slightly smaller than L_(x) in the x direction. The quantity L_(x) must be considered as an upper limit for the dimension of the object in the x direction. The same definition is used for the y direction: choose L_(y) has the upper limit for the dimension in the y direction; in that case:

    Δk.sub.y =2π/L.sub.y                              (13).

The value of the amplitude G_(y) of the gradient G_(y) (t) can now be determined as follows: (a) for a squarewave varying gradient: ##EQU33## because the total surface must be covered in one half period; furthermore, in accordance with the expressions (12) and (13) ##EQU34## It follows therefrom that ##EQU35## (b) for a sinusoidal gradient: ##EQU36## in which t'=t/t_(m) It follows therefrom that ##EQU37## (c) analogously, for a sawtooth or a "triangular" function: ##EQU38## However, it is to be noted that, because the gradient fields are usually generated by means of coils, use is preferably made of sinusoidally alternating gradients. The other types of periodically varying gradients exhibit acute transitions which impose practical problems when coils are used.

The method in accordance with the invention, however, is not restricted to the measurement of one line additional to the reference line L1. The method also enables the simultaneous measurement of more than two lines. FIG. 4 illustrates the case in which three lines (L₁, L₂, L₃) are simultaneously measured. The requirements imposed are again analogous to the requirements imposed in the above case concerning the simultaneous measurement of two lines, i.e. as regards the cancellation of the applied additional phase coding as well as regards the amplitude of G_(y). Thus, for the simultaneous measurement of M lines (M>1) with a stationary gradient G_(x) and a gradient G_(y) which varies in time, the amplitude G_(y), (a) must be given for a squarewave gradient by ##EQU39## (b) must be given for a sinusoidal gradient by ##EQU40##

The spacing between the various lines should again amount to Δk_(y). The distance between a sampling point and the reference line is proportional to the surface enclosed by G_(y), taken from the beginning of the sampling interval until the instant at which the sampling operation is performed. This is illustrated in FIG. 5 for the case involving 3 simultaneously measured lines and a sinusoidally alternating gradient. Therefore, in FIG. 5 Δk_(y) must be proportional to 0₁ and 2 Δk_(y) must be proportional to 0₁ +0₂, and 3 Δk_(y) must be proportional to 0₁ +0₂ +0₃. This requirement has consequences as regards the instants t_(i) at which the points on the various lines L_(i) are measured.

Assume that M (M<N_(y) and M>1) lines are simultaneously measured, so that an N_(x) ×M matrix is determined. The distance between the i^(th) line (i=1, 2, . . . M) and the reference line should preferably amount to (i-1)k_(y).

The distance d(L₁, L_(i)) is related to the surface area which is described by the gradient during the time elapsed between the beginning of the sampling interval and the instant of a measurement on a non-reference line L_(i). For a sinusoidally varying gradient field yields ##EQU41## wherein t'=t/t_(m) and t₁ '=t_(i) /t_(m) and t_(m) is the sampling interval on a reference line. Because a sample of the M^(th) line is taken at the moment t_(M) =t_(m) /2 it can be deduced that: ##EQU42## It follows therefrom that ##EQU43## and on the other hand that ##EQU44## From the expressions (19) and (20) it follows that: ##EQU45## Substitution of values for M and the associated value of i in the expression (22) reveals that if M≦3, sampling can be performed equidistantly in time. For M>3, the requirement of expression (21) results in sampling which is not equidistant in time. This can be simply illustrated on the basis of the example M=4, i=1, 2, 3, 4.

    ______________________________________     i            cos (2π t.sub.i /t.sub.m)                             t.sub.i /t.sub.m     ______________________________________     1             1         0     2             1/3       0.19     3            -1/3       0.30     4            -1         0.50     ______________________________________

These points are shown in FIG. 5.

For a squarewave gradient, the measuring points are equidistant for each value of M, because G_(y) has a constant value throughout the half period. ##EQU46## The same requirement as regards the linear increase of the surface area from one sampling operation to another, is of course also applicable to a sawtooth alternating gradient G_(y) where the sampling is no longer equidistant for values of M larger than 2.

Analogous to the foregoing description, it can be deduced for a sawtooth alternating gradient magnetic field that: ##EQU47##

For the purpose of illustration, the cases M=3 and M=4 will be considered for a sawtooth alternating gradient G_(y).

    ______________________________________     (a) M = 3              (b) M = 4     i       t.sub.i /t.sub.m                            i      t.sub.i /t.sub.m     ______________________________________     1       0              1      0     2       0.35           2      0.29     3       0.50           3      0.41                            4      0.50     ______________________________________

For a sawtooth alternating gradient G_(y), it is then applicable that the sampling is not equidistant for M≧3. It will be clear that each periodic function is satisfactory for G_(y) and that for each periodic function the sampling points must preferably be chosen so that the surface enclosed during the first half period by two successive sampling points is a linear function of time.

Therefore, it is important to carry out the sampling operations which are performed on the non-reference lines at the correct instants t_(i) which are given by the above relations. In order to achieve this object, the device for performing a method in accordance with the invention comprises a control unit (37 in FIG. 2) for controlling the sampling operations at the correct instants t_(i).

Regarding the amplitude of G_(y), it may be stated in general that for the simultaneous measurement of M lines the following is applicable: ##EQU48## (Therein, τ is the instant at which a sampling operation is performed on a reference line).

In other words: at the instant which is exactly situated between the samples on a reference line, (M-1) Δk_(y) must be bridged for simultaneous measurement of M lines. This is no longer generally applicable when use is made of functions G_(y) (t) which are not anti-symmetrical in their zero points. These shapes will be ignored in view of their lack of practical importance.

In total N_(y) lines must be measured for a N_(x) ×N_(y) matrix in the (k_(x), k_(y)) space. When a divider of N_(y) is chosen for M, the image is defined in N_(y) /M measurements. Thus, during the first measurement information is collected on the lines 1 to M, during the second measurement on the lines M+1 to 2M etc. When the information is to be collected on the lines m to m+M-1, such a G_(y) is applied before the sampling that: ##EQU49## is the k_(y) value of the m^(th) line (t is the instant just before the sampling commences).

In accordance with the proposed method, the image is reconstructed as follows. It appears from the foregoing description that for the simultaneous measurement of M lines, the samples must be divided among said M lines in the (k_(x), k_(y)) space. When M is again a divider of N_(y), this is done for all N_(y) /M measurements. It is to be noted that the samples on the N_(y) -N_(y) /M "non-reference" lines are sill in a shift position with respect to the samples on the N_(y) /M reference lines except for the case wherein use is made of a gradient field G_(x) ' as shown in FIG. 3a. In order to ensure that on each row the correct sample is obtained for the Fourier transformation along k_(y) (Fourier transformation of columns) it is necessary to find for the "non-reference" lines the intermediate points which have the same k_(x) coordinate as the points on the reference lines. This can be achieved by interpolation via Fourier transformation. This is done as follows: take the data of a " non-reference" line, perform a 1-D Fourier transformation on these data supplement zeros at the left and the right, and perform a 1-D Fourier back-transformation. The number of zeros added depends on the shift of the sample points on the relevant line with respect to those on the reference line. Subsequently, a 2-D Fourier transformation is required in order to obtain the actual image.

Another possibility is to perform, after the Fourier transformation along k_(x) (which must be performed any way in the 2-D Fourier transformation process), a phase rotation on the values associated with the line (x, k_(y)), that is to say so that the rotation is proportional to x. The proportionality constant in its turn is proportional again to the degree of shifting of the points prior to the Fourier transformation with respect to those on a reference line. By subsequently performing another Fourier transformation along k_(y) on the information thus treated, the pursued actual image will be found.

The imaging of a 3-D object will now briefly be described. The data are collected in the 3-D Fourier transformed space having the coordinates k_(x), k_(y), k_(z). In the 3-D mode of the Fourier zeugmatography, the signal is again measured in the presence of one of the gradients, for example G_(x). During a measurement data are now collected on a line in the Fourier transformed (k_(x), k_(y), k_(z)) space which extends parallel to the k_(x) axis. The k_(y) value and the k_(z) value associated with these lines are determined by the surface below the gradients G_(y) and G_(z), respectively, applied before sampling. Simultaneous measurement of several lines parallel to the k_(x) axis is again possible. This may concern lines having the same k_(z) coordinates or the same k_(y) coordinates. In the former case a gradient G_(y) which alternates in time is present during the measurement of the signal, in addition to a constant gradient G_(x), whilst in the second case G_(z) is the gradient which varies in time. It should be noted that also in the 3-D case a gradient field G_(x) ' as shown in FIG. 3a can be used. The further reconstruction of the image is completely analogous to that in the 2-D mode.

As appears from the FIGS. 3a and 3b, it is useful to make the sampling instants denoted by O and x coincide with the zero points of the curve G₃ or G₄ (reversal of the gradient direction of the gradient magnetic field G_(y)). It is also useful to perform a sampling operation at the instant t_(o) at which the spin echo occurs (this because k_(x) =0 in that case). Consequently, FIG. 6 diagrammatically shows means for the synchronizing of said signals. The time modulated gradient magnetic field G_(y) is generated as follows. The central control means 45 comprise at least one oscillator 51 and a counter 53, the input of which is connected to the oscillator 51 whilst the outputs are connected to the address inputs of a random access memory (RAM) 55. The successive counter positions produce binary control signals on the outputs of the memory 55 which form the amplitudes of a sinusoidal signal. Via a bus 50, the binary numbers of the memory 55 are applied to the generator 21 which comprises a D/A converter 21a and an amplifier 21b for generating a sinusoidally modulated gradient magnetic field G_(y). The control signals are also presented to the control unit 37. The control unit 37 comprises some logic gate circuit 57 which gives an output pulse in response to given binary numerical combinations (for example, 0000=zero crossing or 1111=maximum amplitude), said pulse being presented to an adjustable monostable flip-flop 61, via an OR-gate 59, the output of said flip-flop being connected to the sampling means (29 and 31) via the bus 50. The purpose of the adjustable flip-flop 61 will be described hereinafter.

There are also provided detection means for detecting the reversals of the gradient direction of the G_(y) field. These means comprise a coil 5' which encloses (a part of) the G_(y) field. The coil 5' may form part of the coils 5. The signal which is generated in the coil 5' by the gradient magnetic field which varies in time is applied to an amplifier 63 in order to be amplified and applied to a pulse generator 65 (for example a Schmitt-trigger circuit). The pulses formed by the pulse generator 65 are a measure for the instants at which the gradient direction of the G_(y) field is reversed and are applied to a comparison circuit 67 which also receives the pulses from the flip-flop 61. The comparison circuit 67 enables determination of the time difference between the occurrence of a sampling pulse (61-29, 31) and the instant of reversal of the gradient direction (5', 63), said time difference being displayed by means of an indicator 69. The comparison circuit 67 and the indicator 69, for example, form part of a two-channel oscilloscope, but may alternatively be a set-reset flip-flop and a pulse duration measuring device, respectively, the outputs of the pulse generator 65 and the flipflop 61 being connected to the inputs of the set-reset flipflop, the pulse duration measuring device being connected to the output thereof. The pulse duration of a pulse to be generated by the monostable flipflop 61 can be adjusted on the basis of the time difference thus measured, so that the sampling instant can be advanced or delayed. Obviously, the delays or phase shifts which unavoidably occur in any circuit to be passed by the signals to be compared and the control signals must also be taken into account. For effectively determining the time difference it is useful to admit to the OR-gate 59 only pulses of the logic circuit 57 which generates a pulse in response to the binary number combination (for example, 0000) which represents the zero crossing of the generated sinusoidal signal.

In order to make the spin-echo instant coincident with a sampling instant the control means 45 comprise a further counter 71, connected to the oscillator 51, and a comparator 73 which can be adjusted by means of switches 73'. When the counter 71 reaches a position which corresponds to the value adjusted in the comparator 73, it outputs a pulse which resets the counter 71 to a starting position and which activates, via the bus 50, the high-frequency generator 25 in order to supply a 90° pulse or a 180° pulse (which pulse is to be generated can be determined via a control signal not elaborated herein). When a 180° pulse is supplied the spin-echo instant will have been reached when the counter 71 reaches the value adjusted in the comparator 73 (t_(v1) =t_(v2), see FIG. 3a), the comparator 73 then again supplying a pulse which is also applied to the comparison circuit 67 via a switch 75. Thus, the smallest time difference can be determined between a reversal of the gradient direction (with which the sampling instants should coincide) and the spin-echo instant. The instant of spin-echo can be adjusted (advanced or delayed) by changing the value adjusted in the comparator by an amount which equals half the time difference, multiplied by the oscillator frequency (by varying t_(v1) as well as t_(v2) !) so that sampling instants and the occurrence of spin-echo can be synchronized.

Even though the control means 45, the control unit 37 and the further means for the synchronization of the occurrence of various signals have been described on the basis of discrete circuits, the same result can very well be obtained by utilizing a microprocessor which completes a preprogrammed timing schedule which can be adapted, if necessary, to changing operating conditions by utilizing the signals obtained by means of the coil 5' and the amplifier 63.

In order to render the number of samples per sampling interval t_(m) adjustable (see FIGS. 4 and 5), outputs of various logic gates of the circuit 57 are connected to an input of the OR-gate 59 via a switch 56, 58. A sampling operation can be performed at a given amplitude of the sinusoidal signal by the opening or closing of the switches 56, 58. If the duration of a sampling interval t_(m) is to be longer or shorter, it will merely be necessary to adapt the frequency of the oscillator 51; the relative sampling instants t_(i) within the sampling interval t_(m) will not be disturbed thereby. 

What is claimed is:
 1. A method of determining a nuclear magnetization distribution in a part of a body which is situated in a stationary, homogeneous magnetic field which is generated in a first direction, (a) a high-frequency electromagnetic pulse being generated whose magnetic field direction extends perpendicularly to the field direction of the homogeneous magnetic field in order to cause a precessional motion of the magnetization of nuclei in the body around the first field direction, a resonance signal thus being generated; (b) after which either a first or a first and a second gradient magnetic field is applied during a preparation period, the gradient directions thereof being perpendicular to one another and the field directions being coincident with the first direction; (c) after which a further gradient field is applied for a measuring period, the gradient direction thereof being perpendicular to the gradient direction of at least one of the gradient magnetic fields mentioned sub (b), the field direction being coincident with the first direction, the measuring period being divided into a number of equally large sampling intervals for the periodic extraction of a number of (n) sampled signals from the resonance signal (FID-signal); (d) after which, each time after a waiting period, the steps (a), (b) and (c) are repeated a number of times (n'), the integral of the intensity of at least one gradient field over the preparation period each time having a different value in order to obtain a group of sampled signals wherefrom, after Fourier transformation thereof, an image of the distribution of the induced nuclear magnetization is determined, characterized in that during the measuring period an additional gradient magnetic field is generated whose gradient direction corresponds to the gradient direction of a gradient magnetic field generated during the preparation period and whose field direction coincides with the first direction, the additional gradient magnetic field being periodic in time and having a period which is equal to the sampling interval, the effect exerted on the nuclear magnetization by the additional gradient magnetic field integrated over a sampling interval being zero, at least one additional sampling operation being performed after the beginning and before the end of each sampling interval.
 2. A method as claimed in claim 1, characterized in that at the beginning and during each sampling interval the gradient direction of the additional gradient magnetic field is reversed, sampling operations being performed at least virtually at the instants of reversal of the gradient direction.
 3. A method as claimed in claim 2, characterized in that during each sampling interval at least one further sampling operation is performed between the instants of reversal of the gradient direction of the additional gradient magnetic field, the gradient direction of the additional gradient magnetic field being the same at each further sampling operation.
 4. A method as claimed in claim 3, characterized in that during each sampling interval always M sampling operations are performed, the steps (a), (b) and (c) being repeated m/M times in order to determine the local nuclear magnetization in n×m image points, n and m/M being integer positive numbers, and m>M≧2.
 5. A method as claimed in claim 1 characterized in that during the preparation period two gradient magnetic fields are applied whose gradient directions are perpendicular to one another, the steps (a), (b) and (c) being repeated 1×m/M times, in each sampling interval M sampling operations being performed in order to determine, via a 3-dimensional Fourier transformation, the local nuclear magnetization at the 1×m×n points in a 3-dimensional part of a body, either 1/M or m/M and M being integer positive numbers larger than
 1. 6. A method as claimed in claim 1, characterized in that the additional gradient field is squarewave modulated in time, the sampling instants within a sampling interval being equidistant in time.
 7. A method as claimed in claim 1, characterized in that the additional gradient magnetic field is sinusoidally modulated, its period coinciding with the sampling interval, the sampling instants t_(i) being determined by: ##EQU50## in which: t_(i) is the i^(th) sampling instant,tm is the sampling interval, i is a natural number smaller than (m+1) and larger than or equal to 2, and M is a natural number.
 8. A method as claimed in claim 1, characterized in that the further gradient magnetic field is periodic in time and has a period which equals the sampling interval, its gradient direction always being the same, the further gradient magnetic field being zero during a part of the sampling interval, sampling operations being performed during said part.
 9. A device for determining the nuclear magnetization distribution in a part of a body, comprising:(a) means for generating a stationary homogeneous magnetic field, (b) means for generating high-frequency electromagnetic radiation whose magnetic field direction is directed perpendicularly to the field direction of the homogeneous magnetic field, (c) means for generating at least one first and one second gradient magnetic field whose field directions coincide with the field direction of the homogeneous magnetic field and whose gradient directions are mutually perpendicular, (d) sampling means for the sampling, in the presence of a gradient magnetic field generated by the means mentioned sub (c), of a resonance signal generated by means of the means mentioned sub (a) and (b), after the conditioning with at least one gradient magnetic field generated by the means mentioned sub (c), (e) processing means for the processing of the signals supplied by the sampling means, and (f) control means for controlling at least the means mentioned sub (b) to sub (e) for generating, conditioning, sampling and processing of a number of resonance signals, each resonance signal being each time conditioned during a preparation period, the control means supplying the means mentioned sub (c) with control signals for the adjustment of the intensity and/or duration of at least one gradient magnetic field, the integral of the intensity over the duration of at least one gradient magnetic field being different after each waiting period, characterized in that during sampling the control means apply further control signals to the means mentioned sub (c) in order to generate an additional gradient magnetic field which periodically varies in time and whose period equals the sampling interval, at the end of each sampling interval the effect exerted by the additional gradient magnetic field on the nuclear magnetization integrated over a sampling interval being zero, the gradient direction of said additional gradient magnetic field being perpendicular to the gradient direction of the gradient magnetic field present during sampling, the control means applying the further control signals to the sampling means in order to sample the resonance signal at least once after the beginning and before the end of the sampling interval.
 10. A device as claimed in claim 9, characterized in that the device comprises detection means for detecting reversals of the gradient direction of a modulated gradient magnetic field and a control unit for supplying pulses at sampling instants, the instants of the pulses supplied by the control unit being adjustable by means of a signal generated by the detection means in order to synchronize the sampling instants with said modulated gradient field.
 11. A device as claimed in claim 10, which is suitable for performing a nuclear spin resonance echo technique, characterized in that the detection means supply the processing means with pulses which have been determined by the detection of the instants of reversal of the gradient direction for determining the time difference between the instant of spin echo and an instant at which the gradient direction is reversed and for correcting the period of time between a 90° pulse and a 180° pulse by half the time difference.
 12. A device as claimed in claim 10, characterized in that the control means comprise an oscillator, a pulse counter, a digital memory and logic gate circuits whereby an output of the oscillator is connected to an input of the pulse counter having multiple outputs connected to address input of the memory, in which a sine wave function has been stored, the digital output signals of the memory being fed to a generator for generating a sine-wave modulated magnetic gradient field and being fed to inputs of each of a plurality of logic gate circuits, the output of each of said logic gate circuits being connected to an input of a logic OR gate, an output of which controls the sampling means and each of said logic gates generating an output signal for a different digital output signal of the memory. 